Embolism protection devices

ABSTRACT

Embolism protection devices can be formed with a biocompatible expandable polymer that can expand upon release within a patient&#39;s vessel. Upon release, the structure can be configured to filter flow through the vessel. The material of the embolism protection devices can release one or more biologically active agents, such as a thrombolitic agent, including, for example, tPA. Alternatively or additionally, the embolism protection device can be connected to a tether that elutes one or more biologically active agents.

CROSS REFERENCE TO RELATED APPLICATIONS

[0001] This application is a continuation of copending U.S. patentapplication Ser. No. 10/414,909 to Ogle, entitled “Embolism ProtectionDevices, incorporated herein by reference, which claims priority to U.S.Provisional Patent Application Ser. No. 60/400,341 to Ogle, entitled“Embolism Protection Device,” incorporated herein by reference.

FIELD OF THE INVENTION

[0002] The invention relates to devices for preventing blockage ofpassageways in a patient's body. In particular, the invention relates todevices placed within a vessel, such as a blood vessel or a urinaryvessel, to trap occlusions, such as emboli, for their dissolution orremoval, as well as related methods.

BACKGROUND OF THE INVENTION

[0003] An embolus can be any particle comprising a foreign or nativematerial, which enters the vascular system with potential to causeocclusion of blood flow. Emboli can be formed from aggregated fibrin,red blood cells, collagen, cholesterol, plaque, fat, calcified plaque,bubbles, arterial tissue, and/or other miscellaneous fragments. Embolirange in size from 0.01 cubic millimeters (mm³) to 12.5 mm³ (with anapproximate mean of 0.80 mm³). Emboli characterization is describedfurther described in reference 1. (1) While some references are citedexplicitly in the text, other references are cited in a list at the endof the specification. References listed at the end of the specificationare cited with a number of the reference in parentheses. Thesereferences are incorporated by reference in their entirety as well asspecifically for the particular principle being referenced.

Cardiac Surgery

[0004] Each year there are approximately 800,000 cardiac surgical caseswhich involve cardiopulmonary bypass (CPB) worldwide. (2) Of thesecardiac surgical cases, approximately 48,000 suffer stroke and nearly300,000 experience some neurocognitive disturbance. (3) This is asignificant clinical problem. These complications are due in largemeasure to CPB-generated emboli. The average number of emboli measuredby Trans Cranial Doppler (TCD) in patients undergoing cardiopulmonarybypass is 183 (range 3-947). (2) The majority of emboli end up in thevery distal cerebral tree, the terminal arterioles and capillariescausing microinfarctions, (i.e., loss of blood to surrounding tissue).(4) Pathological evaluation of affected tissues reveals sausage-shapedarterial dilatations known as SCADs. Cerebral microinfarctions can causeconfusion, disturbances of speech, paralysis, visual disturbances,balance disturbances and other neurological deviations. (5) Theseimpairments are frequently short term but can be permanent.

[0005] Whether long term or short term, neurocognitive disturbancestranslate into significant patient care spending. An estimated $750million dollars is spent annually on hospital care for CPB patients andan additional $500 million on long-term hospice care. (2) The averagestay for CPB patients without adverse cerebral outcomes is 8.6 days,while patients with severe adverse outcomes stay an average of 55.8days. (3 and 6) Estimating the average hospital day care cost at$1500/day, extended stays due to embolic events translate on averageinto an additional $60,000 per patient. While daunting, this figurestill fails to include the social and financial burden placed on familymembers upon hospital release. In sum, surgically triggered embolicevents cause high rates of clinically observed neurologicaldisturbances, decreased quality of life and increased patient carespending.

[0006] Cardiac surgical procedures have been correlated directly withneurological injury and stroke due in large measure to the formation ofemboli. Emboli can be generated by surgical maneuvers such ascannulation, aortic manipulation, clamping and unclamping. In fact, bysome estimates, 60% of the total emboli can be associated with clampmanipulation alone. The average number of emboli measured by TransCranial Doppler (TCD) in patients undergoing coronary bypass is 135(range 0-1377), and in patients undergoing vascular surgery, the averagenumber increases to 1030 (range 18 to 5890). The majority of the emboliend up in the very distal cerebral tree, the terminal arterioles andcapillaries causing microinfarcts, (i.e., loss of blood to surroundingtissue).

[0007] Furthermore, mortality increased from 7.4% in patients withoutadverse cerebral outcomes to 30.4% in patients who did have adversecerebral outcomes. A study conducted in Sweden reviewed 7,000 open heartprocedures. Their results with respect to incidence of symptoms as apercentage of all cases are as follows: disturbance of consciousnessincluding slow awakening (1.8%), confusion (5.3%), disturbances ofspeech (1.3%), paresis (2.0%), visual disturbances (1.0%),balance/coordination disturbances (2.3%), seizures (0.2%) and otherneurological deviations (1.8%).

Vascular Surgery

[0008] Emboli formation can also create problems in the realm ofvascular disease, though in these instances the clinical outcome can bepulmonary embolism (PE). Approximately 600,000 people in the UnitedStates suffer from venous thrombi, which could result in a lung embolus.Mortality associated with untreated PE is approximately 30%. (7) Whilesecondary to cardiac surgery, this area represents a Significantclinical indication.

Cardiology and Endovascular Intervention

[0009] Other procedures that can result in emboli include, for example,coronary, carotid, and peripheral interventions. (8) In these cases,particulate matter, including, for example, plaque, debris and thrombus,can form emboli distal to the site of intervention. As a result, bloodflow to the distal vascular bed is diminished and periproceduralend-organ ischemia and infarction can result. Distal embolization oflarge particles produced at the time of such interventions as ballooninflation or stent deployment may obstruct large, epicardial vessels,and smaller particles (as little as 15-100 microns) can causemicroinfarcts and/or myocardial infarctions and left ventriculardysfunction. (8) Myocardial infarction refers to the death of a sectionof myocardium or middle layer of the heart muscle. Myocardial infarctioncan result from at least partial blockage of the coronary artery or itsbranches. Blockage of capillaries associated with the coronary arteriescan result in corresponding microinfarctions/microinfarcs.

Urology and Gastroenterology

[0010] Blockage of other body vessels can occur. For example, kidneystones are one of the most painful of the urologic disorders. Kidneystones also represent one of the most common disorders of the urinarytract; it is estimated that more than I million cases were diagnosed in1996. It has also estimated 10 percent of people in the United Stateswill have a kidney stone at some point in their lives. While most kidneystones pass out of the body without any intervention, stones that causelasting symptoms or other complications require removal. Thus, like theother emboli generated in vascular system, urology could benefit from adevices to remove and resorb calculi in the urinary tract. This calculiis composed of calcium oxalate. Since it is a relatively hard substance,it can cause great pain as it passes through the urinary tract. Suchremoval is often necessary in cases of obstruction, i.e. embolism.

Emboli and Infection

[0011] When foreign material in the stream of flow causes turbulence orlow flow, it has been shown that this increases infection rates.Thrombus not only generates emboli, but also increases the risk ofinfection. (9) Likewise kidney stones can create additional risk forinfection.

[0012] It is evident that a wide variety of embolic events cause highrates of clinically observed symptoms, decreased quality of life andincreased patient care spending.

SUMMARY OF THE INVENTION

[0013] In a first aspect, the invention pertains to an embolismprotection device comprising a biocompatible expandable polymer. Theexpandable polymer can expand upon release within a patient's vesselinto a structure configured to filter flow through the vessel.Corresponding methods relate to delivering an embolism protection deviceinto a patient's vessel.

[0014] In another aspect, the invention pertains to an embolismprotection device comprising a biocompatible resorbable polymer forminga porous structure having a configuration to filter flow through apatient's vessel.

[0015] In an additional aspect, the invention pertains to an embolismprotection device comprising a polymer forming a porous structure and abiologically active agent that elutes from the device when the device isin contact with flow within a patient's vessel. The porous structure hasa configuration to filter flow through the patient's vessel.

[0016] Moreover, the invention pertains to an embolism protection devicecomprising a first section and a compositionally distinct secondsection. The first section has a different average composition from theaverage composition of the second section. Also, the first section andthe second section are configured for placement within a patient'svessel with a substantial fraction of flow passing sequentially throughthe first section and the second section.

[0017] Furthermore, the invention pertains to a system for providingprotection from emboli comprising an embolic protection device and adelivery tool. The delivery tool is configured for releasing theembolism protection device into a vessel from the catheter. The embolismprotection device comprises a biocompatible expandable polymer.

[0018] In addition, the invention pertains to a method for reducing oreliminating adverse effects of an embolus, the method comprisesdelivering an embolism protection device and administering abiologically active agent. The delivering of the embolism protectiondevice can be performed within a vessel of a patient with the devicebeing tethered with a tether such that the embolism protection devicefilters flow within the vessel. The administering of the biologicallyactive agent can be performed through the tether.

[0019] In an additional aspect, the invention pertains to an embolismprotection device comprising a plurality of fibers having surfacecapillaries. The fibers are bound within a structure and have a deployedconfiguration that fills the lumen of a vessel having a diametercorresponding to that of a human vessel.

[0020] In a further aspect, the invention pertains to a system fortrapping emboli comprising a delivery tool comprising a tether and anembolism protection device attached to the tether. The embolismprotection device comprises a fiber with surface capillaries with a sizesuitable for placement within a human vessel.

[0021] In another aspect, the invention pertains to a method fortrapping emboli, the method comprising placing a fiber within apatient's vessel wherein the fibers have surface capillaries.

BRIEF DESCRIPTION OF THE DRAWINGS

[0022]FIG. 1 is a schematic side view of an embolism protection devicewithin a patient's vessel with the left view showing the deployment ofthe device from a deployment apparatus and the right view showing thedevice following deployment.

[0023]FIG. 2 is a schematic perspective view of an alternativeembodiment of an embolism protection device within a patient's vesselwith the left view showing the deployment of the device from adeployment apparatus and the right view showing the device followingdeployment.

[0024]FIG. 3 is a schematic perspective view of another alternativeembodiment of an embolism protection device within a patient's vesselwith the left view showing the deployment of the device from adeployment apparatus and the right view showing the device followingdeployment.

[0025]FIG. 4 is a schematic side view of another alternative embodimentof an embolism protection device within a patient's vessel with the leftview showing the deployment of the device from a deployment apparatusand the right view showing the device following deployment.

[0026]FIG. 5A is a schematic side view of an alternative embodiment ofan embolism protection device within a patient's vessel followingdeployment.

[0027]FIG. 5B is an end on view of the device of FIG. 5A viewed alongline B-B of FIG. 5A.

[0028]FIG. 6A is a schematic side view of an alternative embodiment ofan embolism protection device within a patient's vessel with the leftview showing the deployment of the device from a deployment apparatusand the right view showing the device following deployment.

[0029]FIG. 6B is an end on view of the device of FIG. 6A viewed alongline B-B of FIG. 6A.

[0030]FIG. 7A is a schematic side view of an alternative embodiment ofan embolism protection device within a patient's vessel with the leftview showing the deployment of the device from a deployment apparatusand the right view showing the device following deployment.

[0031]FIG. 7B is an end on view of the device of FIG. 7A viewed alongline B-B of FIG. 7A.

[0032]FIG. 8A is a schematic perspective view of an alternativeembodiment of an embolism protection device within a patient's vesselwith the left view showing the deployment of the device from adeployment apparatus and the right view showing the device followingdeployment.

[0033]FIG. 8B is an end on view of the device of FIG. 8A viewed alongline B-B of FIG. 8A.

[0034]FIG. 9 is a schematic side view of an alternative embodiment of anembolism protection device with a tether to facilitate removal within apatient's vessel with the left view showing the deployment of the devicefrom a deployment apparatus and the right view showing the devicefollowing deployment.

[0035]FIG. 10 is a schematic side view showing the use of the tether toremove the device of FIG. 9.

[0036]FIG. 11 is a schematic side view of an embolism protection devicewith two portions having different properties.

[0037]FIG. 12 is a schematic view showing possible positioning ofembolism protection devices within an aorta and corresponding branchvessels.

[0038]FIG. 13 is a schematic view of an embolism protection deviceassociated with an aortic cannula during cross-clamp bypass.

[0039]FIG. 14 is a schematic view of the embolism protection device ofFIG. 13 following removal of the cross-clamp.

[0040]FIG. 15 is a schematic view of an embolism protection devicedeployed in a coronary artery.

[0041]FIG. 16 is a schematic view of an embolism protection device inthe pulmonary artery.

[0042]FIG. 17 is a schematic view of an embolism protection devicespositioned in blood vessels in a patient's leg and arm.

[0043]FIG. 18A is a schematic side view of a two-component embolismprotection device downstream from a plaque deposit.

[0044]FIG. 18B is a schematic view of the device of FIG. 18A followingdeployment of a stent at the plaque deposit.

[0045]FIG. 18C is a schematic view of the removal of one component ofthe embolism protection device of FIG. 18A.

[0046]FIG. 19 is a side view of an embolism protection device associatedwith a guide-wire through which a biologically active agent is deliveredat one or more of locations A, B and C.

[0047]FIG. 20 is a side view of a gripper device to facilitate removalof an embolism protection device.

[0048]FIG. 21 is a photomicrographs of a PET fiber.

[0049]FIG. 22 is a photomicrograph of a PET fiber with grafted with apolyacrylamide hydrogel.

[0050]FIG. 23 is a plot of the standard curve for a tPA ELISA.

[0051]FIG. 24 is a plot of the elution of tPA from a hydrogel as afunction of time, which provides information on the release kinetics.

[0052]FIG. 25 is a diagram showing an in vitro flow loop.

[0053]FIG. 26 is schematic side view of a composite embolism protectiondevice with two materials prior to expansion.

[0054]FIG. 27 is a schematic side view of the embolism protection deviceof FIG. 26 following expansion.

[0055]FIG. 28 is a side view of an embodiment of a mount for supportingan embolism protection device within the flow loop of FIG. 25.

[0056]FIG. 29A is a micrograph of a fibrin emboli recovered from anembolism protection device that released tPA, at a magnification of200×.

[0057]FIG. 29B is a micrograph of the fibrin emboli in FIG. 29A at amagnification of 400×.

[0058]FIG. 29C is a micrograph of a fibrin emboli recovered from anembolism protection device that did not released tPA, at a magnificationof 200×.

[0059]FIG. 29D is a micrograph of the fibrin emboli in FIG. 29C at amagnification of 400×.

DESCRIPTION OF THE INVENTION

[0060] Improved medical devices to capture and/or remove/dissolve emboliand similar particles can incorporate a polymer that expands in anaqueous environment of the body. The emboli have the potential toocclude vessels to form an embolism in a patient. Suitable polymersinclude, for example, hydrogels and memory polymers that resume a memoryshape upon exposure to a stimulus such as heating to body temperature.In some embodiments, the embolism protection device comprises a blend ofpolymers, such as a structural polymer that provides a framework for thedevice and a hydrogel. The blend of polymers can be in the form of agraft copolymer or the like. The devices can further comprise abioactive agent, such as an agent that is effective to dissolve theemboli. Generally, the embolism protection device is removed followingan appropriate period of time to effectively remove any emboli withinthe device. The embolism protection device generally is used to controlemboli following a medical procedure.

[0061] An embolus as used herein refers broadly to a particle, besidesliving cells, in a vessel within a mammal having a diameter of at leastabout 5 microns. For this determination, the diameter is considered thelargest distance between two points on the surface of the particle.Thus, emboli would encompass emboli within the blood as well as kidneystones and the like. Vascular emboli are thought to be composed almostexclusively of clotted blood. Arterial emboli generated in aorticsurgery or endovascular intervention can be composed of othercomponents, but it is generally believed that they nearly all containsome component of fibrin. See, for example, Reichenspumer et al.,“Particulate emboli capture by an inter-aortic filter device duringcardiac surgery,” J. Thorac. Cardiovasc. Surg. 119(2):233-241 (February2000), Harringer, “Capture of particulate emboli during cardiacprocedures in which aortic cross-clamp is used,” Ann. Thorac. Surg.119(2):701119-23 (February 2000) and Webb, “Retrieval and analysis ofparticulate debris after saphenous vein graft intervention,” J. AmericanCollege Cardiol. 34(2):468-475 (1999), all three of which areincorporated herein by reference. In some embodiments, embolismprotection devices, described herein, can protect the patients in atleast one of three ways: first by filtering emboli, second by dissolvingentrapped emboli and third by bathing the distal myocardial bed or otherdown flow portion of a vessel with a beneficial bioactive agent, such asan embolism dissolving compound, for example, tissue plasminogenactivator (tPA), to help resolve emboli which have become impactedthere.

[0062] The embolism protection device can be delivered, for example, outof a medical implement (catheter or syringe) into the desired vessel,such as a vascular vessel. In some embodiments, the material of thedevice can swell/dilate quickly upon exposure to the aqueous environmentof a patient's body to circumferentially encompass/fill the vessel. Theexpansion of the device can anchor the device within the vessel due tocontact with the vessel wall. In some embodiments, the device can havethe flexibility to conform to the geometry of the vessel. The materialsand structure of the device can be selected to have porosity that wouldallow blood elements, such as white blood cells (about 7-20 microns),red blood cells (8-9 microns) and platelets (2-4 microns), yet collectsemboli. In contrast, emboli generally range in size with diameters fromabout 20 microns to about 3.5 mm, in some embodiments from about 45microns to about 1000 microns and in further embodiments from about 50microns to 200 microns. A person of ordinary skill in the art willrecognize that additional ranges of emboli within the explicit rangesare contemplated and are within the present disclosure. Thus, in someembodiments of interest, the trapping of emboli with a size larger thanabout 45 microns to about 50 microns would be beneficial.

[0063] In some embodiments of particular interest, an embolismprotection device can comprise a polymeric substrate (media, sponge),especially an expandable polymer, such as a swelling polymer, a memorypolymer or a compressed polymer. Specifically, in some embodiments, theembolism protection devices described herein generally comprise aswelling polymer that expands, generally spontaneously, upon contactwith an aqueous solution, such as blood or other body fluids. Swellingis considered broadly in terms of significant changes in dimension dueto an absorption or other intake of fluid/liquid into the structure ofthe material, such as with a sponge, a hydrogel or the like. Hydrogelsare generally hydrophylic polymers that are nevertheless not soluble inaqueous solutions. Generally, hydrogels are crosslinked to prevent themfrom being soluble. While they do not dissolve, the hydrogels swell withaqueous solution when in contact with the solution due to the hydophylicnature of the polymer. In additional or alternative embodiments, anexpandable polymer can comprises a memory polymer that resumes a memoryshape upon exposure to a stimulus, such as exposure to body temperature.In other embodiments, the expandable polymer can comprise a compressiblepolymer that expands upon release of a confining force such as theconfinement provided by a sheath or the like. Furthermore, the embolismprotection device can comprise additional polymers and/or other materialto introduce desired properties to the device.

[0064] Thus, in some embodiments of interest, the devices have acomponent of an expandable polymer to fill the inner luminal space ofthe vessel. In addition, copolymers and/or polymer blends can be used inwhich one or more expandable polymers is combined with other monomerand/or polymer moieties to combine the properties of the differentelements. For example, block copolymers, such as graft copolymers, canbe used to combine polymer units into a combined material thatincorporates properties of the respective polymers. Some embodiments ofswelling polymers include, for example, hydrogels, which can expandlarge amounts upon contact with aqueous solutions. Various hydrogelssuitable for medical applications are known in the art, and particularembodiments are described further below.

[0065] Additional polymers, such as polyesters, polyurethanes, modifiedpolyurethanes, and polycarbonates, within a copolymer or a polymer blendcan provide mechanical strength to the composite material. The embolismprotection device can comprise one or more additional materials, asdesired, to provide particular structural or functional features. Forexample, the outer surface can comprise a material, such as an adhesiveor a fabric that expands with the material but contributes to anchoringof the device to the wall of the vessel. Some embodiments could containmultiple materials for modifying the composition and/or the structure,as desired.

[0066] With appropriate sizing, the embolism protection device can beapplied to any size vessel of a patient. The patient can be any animal,generally a mammal, with particular interest in humans, farm animals andother domestic animals. The devices generally have an ability to conformto irregularly shaped portions of a vessel. Thus, this invention couldbe used for a vascular surgery to prevent a clot, which could causeparalysis, amputation, surgical vascular intervention, otherneurological impairment or death. Due to complications from emboli, suchas a thrombus, there is a significant clinical need for an effectiveprotection from emboli and resulting embolisms. For example, significantpotential applications pertain to coronary intervention following AcuteMyocardial Infarct (AMI). These cases can represent 25% of all coronaryinterventions (as reported at GW Stone Lennox Hill Hospital) due inlarge part to the commonly thrombus-laden lesions found in AMI patients.Due to the flexibility of some embodiments of devices described hereinand the speed at which they can be applied, an embolism protectiondevice can be applied in a wide range of circumstances. In cases such asa broken hip, deployment of the embolism protection device could bepreformed as an emergency procedure to prevent clot formation forpatient's with pro thrombotic disease which are known to clot. While thefocus of the discussion herein focuses on material within blood vesselsand the like, there is also interest in and prevention of occlusion ofother biological vessels in a patient. In particular, the embolismprotection device can be used in other vessels of a patient, such asurinary tract vessels.

[0067] In some embodiments, a biologically active agent can be releasedby way of the embolism protection device. For example, the biologicallyactive agent can be released from a reservoir within the embolismprotection device either quickly and/or in a gradual fashion.Additionally or alternatively, the embolism protection device can beconnected during a procedure to an external source of biologicallyactive agent that is released in a desired dose at or near the embolismprotection device. For embodiments in which the embolism protectiondevice comprises a reservoir of biologically active agents, the embolismprotection device can also elute a biologically active agent from one ormore materials, which could aid in neurological/vascular diseaseprevention associated with surgical. In some embodiments, the reservoirof biologically active agent is physically trapped within the materialsuch that it is released quickly by expansion of the material upondelivery of the device. In other embodiments, the biologically activeagent is eluted gradually by diffusion out from the material in which itis embedded or released gradually by degradation of the material. Insome embodiments, the embolism protection device remains connected to awire following delivery in which the wire has a small inner lumenthrough which the biologically active agent is delivered. The deliverythrough the wire can be at a controlled time and rate, for example, witha syringe, peristaltic pump or the like.

[0068] Some embodiments have one or more emboli dissolving agentsreleased locally to reduce the emboli. These agents can be thrombolyticagents such as tissue plasminogen activator (tPA) or urokinase, or theagents can release mild acid (possibly along with a neutralizing base,such as bicarbonate) or anti-calification enzymes such as osteopontin toresorb calcific plaque. In other embodiments, the devices can release O₂and/or sugars to nourish the patient's brain cells. In otherembodiments, the device can release vasodilators such as NO or heparinto increase the available O₂ transport. In other embodiments, the devicecan release growth factor, which could improve healing or create newvessels. In further embodiments, the device can release viral vectors,which transfected the surrounding cell to up regulate the release apolypeptide compound for extended therapy (e.g., tPA). Specifically, forprotein/polypeptide based agents, the delivery of a gene (nucleic acid)encoding the agent in a vector, such as a viral vector, to promote invivo expression of the protein is an alternative to the delivery of theprotein itself. Delivery of vectors for desired polypeptides isdescribed further below. The device similarly can be designed to releasea plurality of these agents.

[0069] In some embodiments, the material of the device or a portionthereof can be selected to slowly resorb over time. In theseembodiments, the device can be left within the patient rather than beingremoved. In some embodiments, even if a portion of the resorbablematerial were to dislodge from the aggregated material of the device,the resorbable material can still have the same porosity thus be able tofilter while providing flow further up the vascular tree. Resorbablematerials within the embolism protection device could be tuned todissolve over a time range from a very short time to a very long timeafter surgery, as desired. In some embodiments; an imaging approach candetermine the presence of calcified plaque trapped within the embolismprotection device, which would then be removed surgically. In someembodiments a string/tether can be attached to the device for extractionof the device. This attachment can act to reduce the luminal size of thedevice upon extraction for some embodiments of the device. In someembodiments, an extraction device, such as a gripper or the like, can beused to faciliate the removal of the embolism protection device byphysically compressing the embolism protection device.

[0070] Thus, the embolism protection devices described herein can beeffective to reduce or eliminate damage resulting from emboli incircumstances in which potential damage may be indicated by theperformance of particular medical procedure, from the identification ofdiseases and/or by injuries to the patient. The material properties ofthe device provide great flexibility in the design of the device withrespect to different potential ways of handling the emboli. Through theuse of swellable/expandable polymers, the devices can be very versatilewith respect to convenience of delivery, conformability to a wide rangeof vessels and uniform performance in a range of environments. Bycombining biologically active agents with the devices, the improvedstructural features can be combined with the ability to delivertreatments to a localized environment.

Embolism Protection Device Structures

[0071] The embolism protection devices can have various sizes and shapesboth with respect to the exterior surface before and after deploymentand with respect to the arrangement of the materials through the crosssection of the structure. The shape of the exterior of the device caninfluence the nature of the deployment, removal and/or performance ofthe device. The nature of the arrangement of the material across thedevice generally is formulated to be consistent with the maintenance offlow through the device while capturing emboli over an appropriate sizesuch that they do not flow past the device.

[0072] With respect to the shape of the exterior of the device, thisshape can be, for example, generally spherical, cylindrical, concave, orsaddle shaped. A generally spherical or other shaped device maynevertheless have a roughly irregular surface contour about an averageoverall shape, which can orient and adjust to the vessel inside wallupon expansion. Some representative examples are provided below. Anyparticular device generally can conform to the size and shape of theinside of the vessel. While the particular device size depends on thesize of the particular vessel, an embolism protection device followingexpansion within the vessel of a human patient general can have adiameter perpendicular to the flow direction from about 50 microns toabout 35 millimeters (mm), in additional embodiments from about 100microns to about 9 mm and in further embodiments, from about 500 micronsto about 7 mm. A person of ordinary skill in the art will recognize thatadditional ranges of device diameters within the explicit ranges arecontemplated and are within the present disclosure.

[0073] The texture of the outer surface can reflect the structure of theinterior of the device, or the texture of the exterior of the device canbe altered to provide a particular surface texture. For example, thesurface of the device may be porous to reflect the porosity of thedevice generally to the flow. Alternatively, the surface can be treatedto alter the texture and/or covered with a material, such as a fabric,to present an alterative surface contacting the inner surface of thevessel. For example, a fabric cover over the exterior can improve thegripping of the vessels interior surface without damaging the vesselwall. Suitable biocompatible fabrics can be used, such as those formedfrom polyesters.

[0074] Once the embolism protection device is positioned within avessel, appropriate flow should be maintained through the device whileemboli are trapped. Thus, with respect to the flow direction, the devicehas controlled porosity. This controlled porosity can be established bythe nature of the material and/or by the particular structure.Specifically, the polymer density and composition within the device canlead to a distribution of pores such that desired flow is provided whileemboli are trapped by the lack of pores with a diameter large enough forthe emboli to pass. In some embodiments, the device comprises acomposite of two structures/materials with different pore sizes fromeach other. For example, the device can comprise a first material withan average pore size following expansion of the device between about 150microns and 300 microns to be positioned approximately downstream and asecond material with an average pore size of about 50 microns to bepositioned approximately upstream. Alternatively or additionally, thepolymers can be specifically arranged to have a structure that directlyleads to pore sizes with desired sizes one the device expands within thevessel. For example, the polymer can form tubes with selected diametersthat orient along flow direction of the vessel, as described furtherbelow.

[0075] In general, the desired filtering properties and correspondingaverage pore sizes and pore size distributions of an embolism protectiondevice may depend on the particular location of the particular vessel inwhich it is delivered. However, for many applications it can bedesirable to block the flow of a substantial majority of particulateswith a diameter of at least about 0.2 mm while allowing the flow of asubstantial majority of particulates with a diameter of no more thanabout 0.001 mm, and in other embodiments, to block the flow of asubstantial majority of particulates with a diameter of at least about0.1 mm while allowing the flow of a substantial majority of particulateswith a diameter of no more than about 0.01 mm. A person of ordinaryskill in the art will recognize that additional ranges of filteringability within the explicit ranges are contemplated and are within thepresent disclosure. A substantial majority of particulates can beconsidered to be at least about 99 percent.

[0076] In some embodiments, it is desirable to remove the embolismprotection device at some period of time following deployment. Since theembolism protection device expands to contact the interior of the vesselwalls, it may be desirable to introduce structures that facilitate theremoval of the device. For example, the device can comprise one or moretubes, sheaths, rigid extensions, wires, strings, filaments, tethers orthe like appropriately positioned for extracting the device. In someembodiments, the strings are placed such that pulling on the stringtends to contract the device to reduce or eliminate friction on thevessel wall. For example, the strings can be positioned at or near theouter edge of the device that contacts the vessel wall such that pullingon the string tends to pull the exterior of the device toward the centerof the vessel. Tethers and the like also can be useful to maintain anembolism protection device at a delivered position within a vessel.Thus, with a tether or guide wire to maintain the position of theembolism protection device against flow within the vessel, the devicemay or may not exert significant force against the inner wall of thevessel.

[0077] In addition, an extractor device can be positioned with acatheter or the like near the embolism protection device. For example,the extractor can comprise a gripping element that grips the device toreduce its dimensions by physical force such that the embolismprotection device can be removed through a catheter or the like. Aspecific embodiment of a gripping device is described in the examples.Similarly, an extractor can comprise a sheath or the like. The embolismprotection device can be tapered such that an end of the expanded devicefits within the sheath. Then, pulling the device relative to the sheath,such as using a tether or the like, can compress the device within thesheath for removal of the device within the sheath from the patient.Similarly, the device can be twisted in a cork-screw type fashion todecrease the diameter of the device due to the torque and thecompressible nature of the polymers. Similar approaches can be used forplacement of the devices within a sheath for delivery of the device. Forembodiments of embolism protection devices intended for removal from thepatient, it may be desirable to have a smaller porosity toward thevessel wall relative to the porosity away from the vessel wall to reducethe possibility of emboli escaping from the device during the removal ofthe device from the patient. A specific embodiment with this structureis described further in the examples below.

[0078] Referring to FIG. 1, the left view displays an amorphous,generally spherical embolism protection device 100 adjacent a catheter102 within a vessel 104. The right hand view in FIG. 1 shows device 100following expansion to fill the lumen of vessel 104. The arrow indicatesa temporal advance over which device 100 swells across the lumen ofvessel 104. In this embodiment, device 100 has a random array of fibrouspolymer forming the interior of the device 100. In an alternativeembodiment, embolism protection device 110 has a cylindrical shape witha random interior polymer structure 112, as shown in FIG. 2. In thisembodiment, device 110 has an outer surface covered with a fabric 114excluding the flow ends through which the flow of the vessel passes.Referring to further alternative embodiment in FIG. 3, embolismprotection device 120 has a generally cylindrical shape with a polymermatrix 122 that is approximately arranged on a grid. The outer surfaceof the cylinder is covered with fabric 124 with the ends of the cylinderexposed, i.e., free of the fabric. If fabric 124 has a sufficiently openweave, the fabric may also cover the ends of the cylindrical structure.

[0079] As noted above, the embolism protection device can have a concaveshape along the direction of the flow. Referring to FIG. 4, embolismprotection device 130 has a generally bullet shape with the fluid floworiented along arrow 132. Device 130 may or may not have a hollowed outinterior along the concave surface. A saddle shaped embolism protectiondevice 140 is shown in FIGS. 5A and 5B. In the side view of FIG. 5A, thedirection of fluid flow is indicated by arrow 142. Device 140 has aconvex central portion 144 with an outer collection portion 146. In thisembodiment, device 140 has a cuff 148, which for example can be formedfrom rolled fabric or other polymer material, for contacting the wall ofvessel 104. Force from the flow tends to force emboli 150 away fromcentral portion 144 toward outer portion 146. An end view is shown inFIG. 5B. A bioactive agent, such as an thrombolytic agent, can belocated at outer portion 146 for concentration at the location ofemboli.

[0080] Referring to FIGS. 6A and 6B, embolism protection device 154 hasan expandable outer section 156 that forms a hole 158 in the center uponexpansion. This embodiment generally is intended to trap a largerembolism. While it is possible to design device 154 to provide some flowthrough outer section 156, generally this device is removed shortlyfollowing the capture of a larger embolism since flow can besignificantly reduced due to the embolism. A variation on thisembodiment is shown in FIGS. 7A and 7B. In this embodiment, embolismprotection device 160 has polymer elements 162 that extend through acentral core 164 within an outer ring 166. Polymer elements 162 create afilter that traps larger elements from the flow. Polymer elements may ormay not swell upon contact with an aqueous solution, although outer ring166 swell to expand to the wall of vessel 104.

[0081] Referring to FIGS. 8A and 8B, embolism protection device 170 hasa plurality of tubular shaped passages 172 along the length of thegenerally cylindrical device. The outer cylindrical surface 174 may ormay not be covered in a fabric. Furthermore, the tubular shaped passages172 can be formed from a collection of polymer tubes assembled togetherto form the structure or from tubular openings through a polymer matrix.

[0082] As noted above, an embolism protection device as described hereincan comprise a tether or the like to facilitate removal of the deviceafter sufficient time to protect against emboli. Referring to FIG. 9,embolism protection device 180 comprises two strings 182, 184 thattether device 180, although a single string or greater than two stringscan be used. Device 180 is shown in an unexpanded configuration in theleft wide of FIG. 9 and in its expanded form in the right side of FIG.9. By providing two strings, pulling on the strings tends to draw thestrings together to contract the device if the strings are in a spacedapart attachment on the device. As shown in FIG. 10, tension on strings182, 184, as indicated by arrow 186, is resulting in contraction indiameter of device 180 and corresponding movement from right to left.Other configurations of strings can be used to tether an embolismprotection device to facilitate removal and to contract the device,which may depend on the particular shape and structure of the device.

[0083] The embolism protection devices can comprise a composite ofdifferent structures, materials and/or bioactive agents. In particular,in these embodiments, the embolism protection device can haveidentifiable portions that are compositionally distinct with respect tothe average composition within the portion. In some embodiments, theportions are positioned such that the flow or a substantial fraction ofthe flow passes sequentially through one section followed by anothersection. In such a configuration, generally at least about 25% of theflow volume and in other embodiments at least about 80% of the flowvolume flow sequentially through the first portion followed by thesecond portion. A person of ordinary skill in the art will recognizethat additional ranges of flow within the explicit ranges arecontemplated and are within the present disclosure.

[0084] For example, as shown in FIG. 11, embolism protection device 190comprises an up-flow portion 192 and a down-flow portion 194, where flowthrough the vessel is indicated with arrow 196. In some embodiments,up-flow portion 192 can elute, for example, a weak acid that tends todissolve at least some emboli, while down-flow portion 194 can comprisea buffer that neutralizes the weak acid as it flows downstream.

[0085] In some embodiments, up-flow portion 192 and down-flow portion194 can be separable. Thus, for example, up-flow portion 192 can providea mesh, a sponge-like material and/or another porous material across theflow to collect emboli for subsequent removal. Down-flow portion 194 canbe a tubular structure that does not significantly alter the flow, butelutes a bioactive agent, such as tPA and/or NO. Since the portionsseparate, up-flow portion 192 can be taken from the vessel to remove thetrapped emboli while down-flow portion remains in the vessel to elutebeneficial agents. In alternative embodiments, the positions of the twoportions can be reversed with respect to the flow and the portion to beremoved, i.e., the down-stream portion can be removed to leave theup-stream portion. In variations on this embodiment, the down-flowportion can also trap emboli. Thus, following the removal of the up-flowportion, the down-flow portion can be effective to trap emboli. Thedown-flow portion can be formed from a bioresorbable material such thatit dissolves at a desired rate.

[0086] The structures in FIGS. 1-11 are representative structures forthe embolism protection device. Additional structures can be formedbased on the disclosure herein.

[0087] In some embodiments, the embolism protection devices can bedistributed along with other components that can be used along withother instruments that facilitate the use of the embolism protectiondevice. For example, an embolism protection device can be distributedalong with delivery tools, retraction devices, tools for the delivery ofbiologically active agents, instructions and other suitable tools.Suitable delivery tools include, for example, sheaths and/or cannulainto which the embolism protection device can be placed for deliveryalong with other catheter components that can facilitate the delivery ofthe device. Suitable retraction devices that facilitate the removal ofthe embolism protection device are described herein, which can bedistributed with the embolism protection device. For the delivery of abiologically active agent along with the embolism protection device, aguide-wire with a hollow core and/or a cannulated syringe can bedistributed with the embolism protection device. The cannulated syringecan be connected to the guide-wire for the delivery of a biologicallyactive agent in the vicinity of the embolism protection device withinthe patient's vessel. The guide-wire may or may not be associated withthe embolism protection device as a tether. In addition, the embolismprotection device can be distributed with instructions, which can taketo form of written instructions and/or electronic copies, including, forexample, a direction to a suitable web site. The commonly distributedelements can be distributed in one or more containers, for example, as akit. While the embolism protection device generally is disposablefollowing removal from the patient, the other individual elementsdistributed with the embolism protection device may or may not bereusable following sterilization.

Materials

[0088] The embolism protection device can be fabricated frombiocompatible materials, which can be delivered in vivo with limitedvessel trauma, and, in some embodiments, can possess the ability tobreak down entrapped emboli. Some materials comprise a matrix, which canbe capable in some embodiments of expanding upon delivery, capable ofwithstanding in vivo pressures to minimize movement and/or capable ofdelivering thrombolytic agents in a controlled fashion. The embolismprotection devices described herein generally comprise one or morepolymers with generally at least one polymer being an expandablepolymer, e.g., swelling, shape adjusting and/or compressed, upon releasein a vessel in a patient's body. Various suitable polymers can be usedfor swelling including, for example, highly absorbing hydrophilicpolymers (e.g., polyether-polyurethane) or hydrogels, while shapeadjusting polymers can be memory polymers as described below. Compressedpolymers are physically deformable or elastic such that they can besqueezed into a sheath or the like for delivery into a vessel of thepatient, such that the polymer expands following removal from thesheath. In some embodiments, the device comprises a plurality ofpolymers in a blend and/or a plurality of monomers in a copolymer, whichcan be a block copolymer. An advantage of using a plurality of polymersincludes, for example, the ability to introduce propertiescharacteristic of each individual polymer or of each monomer groupincorporated into a copolymer.

[0089] In general, the expansion of the polymer and the correspondingdevice can occur spontaneously following the application of anappropriate stimulus. The appropriate stimulus can be, for example,contact with an aqueous fluid, release of constraining forces, such asapplied by a sheath, and/or heating to body temperature. The expandablenature of at least some of the materials of the embolism protectiondevices inherently allows them to conform to the patient's vessel. Thus,minor variation in the vessel size and shape along the extent of thedevice can be handled appropriately by minor variations in the expansionof the device at different locations. However, for vessel or branchpoints of vessels that have a more complex non-cylindrical structure,the device shape can be formed specifically to adjust for delivery atthe particular shape of the vessel. In these embodiments, the deviceexpands into a predictable non-cylindrical shape due to the pre-shapingof the device.

[0090] Suitable swelling polymers can include, for example, hydrogelsand sponge materials. The amount of swelling that takes place uponcontact with an aqueous medium can range from about 10 percent togreater than a factor of twenty times (i.e. 2000 percent), in someembodiments from a factor of fifty percent to a factor of fifteen times,in other embodiments from a factor of two times to a factor of twelvetimes, and in further embodiments from a factor of seven times to afactor of ten times. A person of ordinary skill in the art willrecognize that addition ranges of swelling within the explicit rangesare contemplated and are within the present disclosure. The desireddegree of swelling may be selected to provide the desired degree ofpressure between the device and the vessel wall following deployment aswell as accounting for the relative sizes of the vessel and the deliverydevice, such as a catheter. The device may further be compressible apartfrom the expansion from hydration such that release of the device fromthe delivery system results in an expanded device relative to itspre-delivery size. However, generally some swelling or other expansionis used to maintain the device within the vessel in which the swellingprovides pressure against the vessel wall. Generally, the devicecontacts the wall over a significant portion of its outer surface suchthat the force against the vessel is distributed over a significantarea. Since the force generally is spread over a significant area, themagnitude of the force can be correspondingly reduced such that there isless potential for damage to the vessel wall. Furthermore, as describedabove, the embolism protection device can be tethered in place such thatlittle or no force is needed between the device and the vessel wall tohold the device at the delivered position.

[0091] Hydrogels are hydrophylic polymers that generally are crosslinkedto make them insoluble in an aqueous solution. Due to the hydrophylicnature of the polymer functional groups, the hydrogels draw aqueoussolution into the polymer material. Suitable hydrogels include, forexample, crosslinked forms of polyacrylamide,poly(hydroxyethylmethacrylate) (PHEMA), cellulose derivatives,poly(vinyl alcohol) and polyethylene glycol. The degree of crosslinking,composition and other features can be used to control the degree ofswelling. Some hydrogels can swell by a factor of 1000 percent or moreupon contact with an aqueous solution. Several qualities of hydrogelshave made them an attractive option in the medical device arena. Thesequalities include their ability to work as a protective barrier for openwounds and absorb excess fluids. In addition, hydrogels arebiocompatible, nontoxic, and nonthrombogenic, have inherent adhesivenessto tissue and have been shown to deliver drugs in a controlled fashion.(15) Also, the hydrogels can be used to associate with other polymersthat are less biocompatible or more thrombogenic to introduce desirableproperties to the composite.

[0092] Suitable foam and sponge materials include, for example,polyester, aromatic vinyl polymers, polyether, polyurethane and mixturesthereof. Modified polyurethane polymers can be used to improve thebiocomatability of the polymer. See, for example, U.S. Pat. No.6,320,011 to Levy et al., entitled “Derivatized PolyurethaneCompositions Which Exhibit Enhanced Stability In Biological Systems AndMethods Of Making The Same,” incorporated herein by reference. Thefoam/sponge materials can be formed, for example, in a molding processwith a blowing agent. An example of a polymeric sponge material andmethods of forming the sponge material are described further in U.S.Pat. No. 4,456,706 to Siedenstrang et al., entitled “Molding compounds,Sponge Articles Produced Therefrom And Process Of Production,”incorporated herein by reference.

[0093] Compressible biocompatible polymers include, for example, foamproducts useful for biological applications. For example, hydrophilicpolyether-polyurethanes and polycarboxylate polyurethanes can be used toform foam that are compressible while absorbing a large amount ofaqueous solutions. U.S. Pat. No. 5,914,125 to Andrews et al., entitled“Wound Dressing,” incorporated herein by reference, describes ahydrophilic polyether polyurethane foam material with an adsorptivecapacity of at least about 10 times its own weight. In addition,published U.S. patent application Ser. No. 2002/0072550A to Brady etal., entitled “Biostable Polyurethane Products,” incorporated herein byreference, describes foam materials with a void volume of 85% that areformed from either polyether polyurethanes or polycarbonatepolyurethanes. In addition, polyurethanes poly-vinyl polymers can alsobe used to form biocompatible foams. U.S. Pat. No. 4,550,126 to Lorenzet al., entitled “Hydrophilic, Flexible, Open CellPolyurethane-poly(N-vinyl lactam) Interpolymer Foam And Dental AndBiomedical Products Fabricated Therefrom,” incorporated herein byreference, describes a foam with a good ability to absorb aqueousfluids. These foams can be formed into appropriate shapes for use in theembolism protection devices described herein.

[0094] In some embodiments, the embolism protection device can comprisea polymer blend and/or copolymer as other polymers alone may not provideall desired functions or properties. Specifically, it may be desirableto use at least one polymer to provide additional mechanical strength tothe device within the flow and and an expanding polymer, such as ahydrogel, to introduce the expansion of the device upon delivery and toprovide for control of the porosity of the expanded device. Suitablestructural, biocompatible polymers for these blends include, forexample, polyesters, such as polyethylene terephthalate, andpolyurethanes, such as polycarbonate-polyurethanes, polyetherpolyurethanes, silicon-polyether-urethanes andsilicon-polycarbonate-urethanes. For embodiments in which the expansioninvolves a swelling polymer, these polymer blends comprises from about25 weight percent to about 95 weight percent structural polymer relativeto the total polymer of the blends, and in further embodiments fromabout 35 to about 85 weight percent structural polymer relative to thetotal polymer of the blends. In embodiments in which expansion involvesa shape changing polymer and/or a compresses polymer, a polymer blendgenerally would comprise at least about 40 weight percent expandingpolymer and in other emboidments at least about 50 weight percentexpanding polymer. Similarly, the proportions can be considered withrespect to the weight of blocks of a block copolymer. A person ofordinary skill in the art will recognize that additional ranges ofstructural polymer proportions within the explicit ranges arecontemplated and are within the present disclosure.

[0095] In some embodiments, the embolism protection device can comprisea biodegradable shape adjusting or memory polymer. These polymer cantransition to a memory shape upon application of a stimulus, such as atemperature change. In particular, biodegradable polymers are availablethat resume a memory shape upon placement at body temperature or pH. Thememory shape can be an expanded form that would extend the device acrossthe lumen of the vessel. Thus, the memory polymer can expand theembolism protection device without the assistance of a swelling polymer,although the device may or may not comprise a blend or copolymer withthe memory polymer and a hydrogel or other swelling polymer. Suitablememory polymers are described further in U.S. Pat. No. 6,160,084 toLanger et al., entitled “Biodegradable Shape Memory Polymers,”incorporated herein by reference. These polymers, in particular, can beused to form devices with a saddle shape, as shown in FIGS. 5A and 5B.In some embodiments, the device with a biodegradable polymer can becombined with an initial amount of tPA and vectors to deliver anexpressible tPA gene to transfect nearby cell to supply tPA on a longerterm basis after the initial tPA with the device has eluted. Thedegradation of the device avoids the need to eventually remove thedevice and the supplies of tPA dissolve emboli such that the device doesnot become clogged with emboli during a more extensive implantation.

[0096] Other suitable memory polymers include, for example, hydrophilicpolymer fibers, including, for example, polyester fibers. Suitablefibers are described, for example, in U.S. Pat. No. 5,200,248 toThompson et al., entitled “Open Capillary Channel Structures, ImprovedProcess For Making Channel Structures And Extrusion Die For UseTherein,” incorporated herein by reference. These fibers can be heatedgently to cause the fibers to curl. The curled fibers can be stretchedstraight at room temperature. Upon heating to body temperature, thefibers resume the curled configuration. By using a bundle of thestretched fibers, the individual fibers of the bundle curl upon deliverydue to body heat/hydration to form a fibrous filter mat that can entrapemboli within the fibrous network. The appropriate number of fibers forthe bundle can be selected empirically to yield the desired packingdensity in the resulting mat and corresponding effective pore size.

[0097] One means of creating copolymers with desired properties is toform a graft copolymer. A graft copolymer is prepared by linkingtogether two different polymers, for example, by way of chemicalinitiation (10) or radiation (11) in the form of ultra violet light,gamma or x-ray irradiation. A graft copolymer can exhibit propertiesclosely related to the two parent compounds. Some copolymer embodimentsharbor the tensile strength and biostability of polyethyleneterephthalate and the super absorbent swelling of polyacrylamide.

[0098] Polyethylene terephthalate (PET) polyester has been usedextensively in medical devices including sutures and large diametervascular grafts with good clinical success. (12) The molecular formulafor PET is H—[O—(CH₂)₂—O—CO—(C₆H₄)—CO]_(n)—R where R can be, forexample, OH (Dacron®) or OCH₃ (terylene), and the chemistry and fibermanufacture is well worked out. The FDA has approved PET for suchimplants as fabric used in suture (temporary implant) or sewing ringsfor heart valves (permanent implant). (13) Given these characteristics,PET is suitable as the base material for an embolism protection device.

[0099] Polyacrylamide belongs to the class of hydrogels known as superabsorbent polymers. These polymers swell in the presence of aqueoussolutions and can increase to 1000 times their original size. (14) Theability of polyacrylamide to swell can contribute significantly to theefficacy of some embodiments of the device design proposed here.However, placing such a material in the vasculature involves appropriatecontrol of swelling parameters to avoid vessel harm from excessiveswelling. In addition, swelling can cause changes in polymer porosity.(30) A pore size that is too small may hinder blood cell flow, while apore size that is too large may allow emboli to pass. The design of thedevice contributes significantly to porosity, however porosityassociated with swelling can also contribute to the function ofentrapping emboli.

[0100] The desirability of polyacrylamide as a material for the devicesdescribed herein stems at least in part from its chemical structure.Polyacrylamide is derived from acrylamide monomer units. The molecularformula is —[CH₂CHCONH₂—]_(n)—. Polyacrylamide is a linear hydrogelwhich can react with many kinds of compounds to produce derivatives ofpolyacrylamide with many valuable properties such as flocculation,thickening and surface activity. (16,29) This reactivity allows foraddition of functional groups, which may alter its physical properties.In addition, there is a group of special polyacrylamide copolymerscalled super absorbent polymers. (17,21) These polymer can absorb waterten to one-thousand fold of their original weight and, under certainpressure, do not dehydrate. During expansion, super absorbant polymersare capable of delivering agents to the surrounding microenvironment,which is a quality useful for delivery of thrombolytic agents fromcorresponding devices. Super absorbent hydrogels are also furtherdescribed in U.S. Pat. No. 6,271,278 to Kinam et al., entitled “HydrogelComposites And Super Porous Hydrogel Composites Having Fast Swelling,High Mechanical Strength, And Superabsorbent Properties,” incorporatedherein by reference. As with PET polyester, polyacrylamide is approvedby the FDA for use in medical adhesives. (18) The FDA approval of thematerial together with its material properties makes polyacrylamide asuitable polymer and/or copolymer for use in the embolism protectiondevices described herein. Polyacrylamide has been used as a controlledrelease vehicle for anti-microbial agents. (28) Extensive studies havebeen conducted on the swelling and deswelling of polyacrylamide. (26)Several factors contribute to the swelling properties of polyacrylamideincluding swelling agent composition, curing time, degree of hydrolysis,temperature and cross-linking. Cross-linking is most intimately tied toswelling, for swelling is described as the process necessary to attainequilibrium between thermodynamic expansion (Flory-Huggins theory, 1953)and the retractive force of the cross-linked structure. There areseveral means to alter cross-link degree and formation includingalteration of preparation physical state (dry vs. wet), cross-linkingduration, and cross-linking agent. A recent study investigated theeffect of several different cross-linking agents on polyacrylamide gelswelling. (27) In brief, a 5×5 cm piece of polyacrylamide gel wasdehydrated and weighed. The sample was then immersed in 100 ml ofdistilled water, and the weight of the samples was taken at 10 minuteintervals. The weight degree of swelling, q, (ratio of the weight of theswollen sample to that of the dry sample) was plotted as a function oftime. Results indicate a greater than six-fold change in weight degreeof swelling simply by altering the cross-linking agent. Control ofpolyacrylamide hydrogel porosity and crosslinked density is describedfurther in U.S. Pat. No. 6,391,937 to Beuhler et al., entitled“Polyacrylamide Hydrogels And Hydrogel Arrays Made From PolyacrylamideReactive Prepolymers,” incorporated herein by reference. By varying thecrosslinking agent, prepolymer properties and the degree ofcrosslinking, the porosity of the hydrogel can be controlled to satisfydesired device parameters.

[0101] In some embodiments, block copolymers can be used to introduce astable form of a polymer blend in which the hydrogel is bonded to astructural polymer. In particular, the hydrogel can be grafted onto thestructural polymer material based on knowledge in the art. Inparticular, polymeric materials have been grafted together using plasma,although other crosslinking approaches can similarly be used. Ahigh-energy plasma technique generates active groups in the polymer,which facilitate the grafting of the second substrate to the first. Thechemical composition of the two materials are complementary to thispotential bonding and have been individually used to generate graftcopolymers. (24) This copolymer matrix has the potential to swell anddevelop significant porosity in a controllable fashion. This reactionresults in the grafting of polyacrylamide onto the (PET) fibers. Thisgrafting can be further or alternatively facilitated with ultravioletcrosslinking. (25) (See Equation 1.)

[0102] Reaction of Polyacrylamide and PET Polyester

[0103] In some embodiments, the embolism protection device comprises abiodgradable/bioresorbable polymers. These embodiments may or may notfurther comprise a biologically active agent that is released by thedegradation of the biodegradable polymer following implantation within apatient. Suitable biodegradable polymers include, for example,polysaccharides, such as polydextran, cellulose and starch, hydroxyethylstarch, derivatives of gelatin, polyvinylpyrrolidone, polyvinyl alcohol,poly[N-(2-hydroxypropyl)methacrylamide], poly(hydroxyacids),poly(epsilon-caprolactone), polylactic acid, polyglycolic acid,poly(dimethyl glycolic acid), poly(hydroxybutyrate), copolymers thereofand mixtures thereof.

[0104] To form the desired structures from the polymers, the polymersduring the crosslinking/grafting step can be molded into the desiredform. Various molding techniques can be used, such as injection molding,casting, compression molding and the like. However, other polymerprocessing approaches can similarly be used, such as extrusion,calendering, blowing and the like. In particular, foam materials can beformed conveniently by extrusion, and composite materials can be formedby coextrusion. In some embodiments, the porosity is introduced througha particulate pore forming agent that is combined with the polymerduring processing and subsequently removed, such as by dissolving theparticles while leaving the polymer intact, to leave the pores. Thenature of the porosity is determines in part from the nature of the poreforming materials. If sponge-like materials are formed by foaming,non-uniform pressure can be applied to the expanding foam to change theresultant porosity.

[0105] Additional materials, such as metals, can be introduced into thepolymer to render the device radio-opaque such that it can be visualizedvia angiography or clinical techniques. Biocompatible metals include,for example, titanium, titanium-nickel alloys, and stainless steel.Guidewires, tethers and the like can also be formed from thesebiocompatible metals and/or biocompatible fibers, which can be formedfrom the same materials as the biocompatible fabrics described below.Also, the embolism protection device can further comprise abiocompatible adhesive, especially on the exterior of the device tofacilitate anchoring of the device at the place of delivery. Suitablebiocompatible adhesives include, for example, commercially availablesurgical adhesives, such as cyanoacralate (such as 2-octyl cyanoacrylatefrom Ethicon Products), fibrin glue (such as Tissucol® from Baxter) andmixtures thereof.

[0106] Also, the exterior can be covered with a biocompatible fabric.Biocompatible fabrics can be formed from a variety of materials, such assilk, nylon and/or polyesters, including, for example, Dacron®polyester. The fabric can be selected to have a porosity smaller thanthe porosity of at least a portion of the remaining device or noporosity, such that trapped emboli generally do not pass through thefabric upon the removal of the device from the patient. Similarly, theembolism protection device can have a coating, such as a polymercoating, which can be formed by stray coating or dip coating a polymersolution or a polymer melt, which forms the polymer coating upon dryingor cooling, respectively. Such a polymer coating may not be inherentlyporous, and desired porosity can be introduced by mechanicallypuncturing the coating with a fine needle or the like or by laserdrilling appropriate pores. A wide variety of lasers with moderate powercan be used for the drilling and conventional optics can be used tofocus the laser beam to produce the desired pore size.

Bioactive Agents

[0107] The embolism protection devices alone provide control over themovements of emboli within the patient's vessel. However, it may bedesirable to combine the mechanical features of the device withbiologically active agents to provide another dimension to thetreatment. The association of bioactive agents with the device can bothprovide treatment to shrink or eliminate emboli within the device and/oralso to deliver a bioactive agent downstream from the device. Suitablebioactive agents include, for example, thrombolytic (anti-thrombogenic)agents, anti-platelet agents, anti-coagulation agents, growth factorsand combinations thereof.

[0108] Suitable thrombolytic agents include, for example, tissue-typeplasminogen activator (tPA), mutated forms of tPA, such as TNK-tPA andYM866, urokinase, streptokinase, staphylokinase, and the like. Inparticular, tPA is a polypeptide that acts upon plasminogen to formplasmin. Plasmin breaks down fibrin, one of the main structural proteinsin blood clots. (22,23) Plasmin also lyses fibrinogen, a precursor offibrin. tPA can be produced according to the method described in U.S.Pat. No. 4,935,368 to Ryotaro et al., entitled “Process For ProducingTissue Plasminogen Activator,” incorporated herein by reference. Aneffective precursor of tPA is described in U.S. Pat. No. 6,001,355 toDowdle, entitled “Pro-tPA For The Treatment Of Thrombosis, Embolism AndRelated Conditions,” incorporated herein by reference. Analogs, i.e.mutated forms, of tPA are known, for example, as are described in U.S.Pat. No. 5,106,741 to Marotti et al., entitled “Tissue PlasminogenActivator (TPA) Analogs,” published PCT application WO 93/20194 to Satoet al., entitled “TPA Analog,” and PCT published application WO 02/22832to Xia et al., entitled “A Cell Line Expressing Mutated HumanTissue-Type Plasminogen Activator, The Constructing Strategy Thereof AndMethods Of Preparing Expressed Protein,” all three of which areincorporated herein by reference. Elsewhere in this applicationincluding the claims, tPA refers to natural tPA, fragments thereof andanalogs thereof that are effective to stimulate the formation ofplasmin.

[0109] Together with a sound materials design, an embolism protectiondevice associated with tPA can be capable of destroying emboliassociated with cardiopulmonary bypass. Recent reports suggest that mostof the emboli generated during cardiopulmonary bypass have a significantfibrin component. (19,20) The body's primary means of degrading fibrinis via tissue plasminogen activator (tPA). tPA is currently in clinicaluse as a remedy for heart attack and stroke (thrombolysis, reperfusiontherapy). This therapy involves delivering tPA through an intravenousline to break up and dissolve a clots in the coronary artery, therebyrestoring blood flow. (21) tPA is of particular interest for use withembolism protection devices described herein given its high specificityfor clot degradation without causing systemic bleeding events.

[0110] Suitable anti-platelet agents include, for example,acetylsalicylic acid, ADP inhibitors, phosphodiesterase III inhibitors,glycoprotein IIB/IIIA inhibitors, adenosine reuptake inhibitors,nitrates, such as nitroglicerin and isosorbide dinitrate, and Vitamin E.Suitable anti-coagulation agents include, for example, heparin,warfarin, and the like. Suitable growth factors include, for example,vascular endothelial growth factor (VEGF) and the like.

[0111] In some embodiments, materials are incorporated into the devicethat form by decomposition a therapeutic composition. For example,nitric oxide (NO) can stimulate beneficial vascular responses. Compoundswith an NONO⁻ functional group can emit nitric oxide followingimplantation of the medical device. Suitable compositions include, forexample, (CH₃)₂CHNHNONO⁻, (CH₃CH₂)₂NNONO⁻, H₂N(CH₂)₃NIJNONO⁻, NaNONONa.The synthesis of 1-(2S-carboxypyrrolidin-1-yl)-oxo-2-hydroxydiazenedisodium salt, 1 -hydroxy-2-oxo-3-carboxymethyl-3-methyl-1-triazineN-methylamide disodium salt, 1-hydroxy-2-oxo-3-carboxymethyl-3-methyl-1-triazine N-methylamide sodiumsalt, the bis(nitric oxide) adduct of L-prolyl-L-leucylglycinamide, andcorresponding protein adducts are described in U.S. Pat. No. 5,632,981to Saavedra et al., entitled “Biopolymer-Bound Nitric Oxide ReleasingCompositions, Pharmaceutical Compositions Incorporating Same And MethodsOf Treating Biological Disorders Using Same,” incorporated herein byreference. Conjugates of heparain, for example with dermatan sulfate,that are effective to prevent thrombosis are described in U.S. Pat. No.6,491,965 to Berry et al., entitled “Medical Device ComprisingGlucosaminoglycan-Antithrombin III/Heparin Cofactor II Conjugates,”incorporated herein by reference. Furthermore, some polymers decomposeto form an acidic moiety, such as polyhydroxybutyrate degrading to3-hydroxyvaleric acid.

[0112] The bioactive agent can be associated with the materials of theembolism protection device by one or more approaches. For example, thedevice can be contacted with a solution of the agent such that the agentcan be infused within the device. The agent is then released, possiblygradually, upon implantation of the device. For example, duringexpansion, super absorbent polymers can be capable of delivering agentsto the surrounding microenvironment, a quality appropriate for deliveryof thrombolytic agents or other bioactive agents. In other embodiments,the bioactive agents are placed in contact with the polymers during thepolymerization and/or crosslinking/grafting steps such that thebioactive agents are incorporated within the polymer matrix. Thebioactive agents then elute following implantation.

[0113] For systemic administration, the therapeutic dose of tPA for ahuman patient can be 0.01 to 80 micro moles (70-8750 ng/ml) but isthought to be most effective at 500-1000 ng/ml. (31) Lower doses may beeffective with local delivery since the local concentration can behigher over the delivery period. An appropriate corresponding dose forlocal delivery can be sustained throughout the time of implant. If thedose is released too quickly, a toxic environment can ensue (>25,000ng/ml for systemic delivery). (32) To determine the initial loadingdose, the release kinetics of tPA from the device can be used to delivera desired dose of tPA or other biologically active agent. An empiricalevaluation of an appropriate dose can be estimated from in vitrostudies, such as the flow loop studies described below, or in animalstudies. In some embodiments, it may be desirable to deliver thebiologically active agent with a suitable biocompatible carrier.Suitable biocompatible carriers can be, for example, a physiologicallybuffered saline. Suitable buffers can be based on, for example, thefollowing compounds: phosphate, borate, bicarbonate, carbonate,cacodylate, citrate, and other organic buffers such astris(hydroxymethyl)aminomethane (TRIS), N-(2-hydroxyethyl)piparazine-N′-(2-ethanesulfonic acid) (HEPES) or morpholinepropanesulphonic acid (MOPS). The ionic strength of the biocompatiblecarrier can be adjusted by the addition of one or more inert saltsincluding, for example, NaCl, KCI and combinations thereof. Preferably,the ionic strength is near physiological values.

[0114] Additionally or alternatively, genes coding for desiredpolypeptide-bioactive agents can be delivered in a vector. The vectorcan be taken up by adjacent cells and expressed as the protein. Suitablevectors are known in the art, and include, for example, viral vectors,plasmids and the like. In particular, a vector encoding tPA can bedelivered through the device. The effectiveness of a vector for tPAexpression in rabbits is described further in Waugh et al., “Genetherapy to promote thromboresistance: Local over-expression of tissueplasminogen activator to prevent arterial thrombosis in an in vivorabbit model, Proceeding of the National Academy of Sciences—USA 96(3):1065-1070 (Feb. 2, 1999), incorporated herein by reference. Vectors, forexample, plasmids and viral vectors, suitable for transforming humancells with appropriate control sequences for expression in human cellsare described further in U.S. Pat. No. 5,106,741 to Marotti et al.,entitled “Tissue Plasminogen Activator (TPA) Analogs,” and U.S. Pat. No.4,935,368 to Ryotaro et al., entitled “Process For Producing TissuePlasminogen Activator,” both of which are incorporated herein byreference.

Use Of the Embolism Protection Device

[0115] Nearly all cardiac surgical procedures and well as certainnon-cardiac procedures and natural events, such as kidney stoneformation, result in the generation of emboli, in the broad sense usedherein. Emboli generation frequently causes life altering, and possiblylife threatening neurological disturbances. The emboli protection devicedescribed herein can be useful for all patients undergoing cardiacsurgery and for other procedures. In some embodiments, the elegantdesign employs a unique combination of FDA approved materials andtherapeutic agents to provide an easy to use and effective means ofcontrolling embolic events. At some point following the delivery of anembolism protection device, it may be desirable to remove the device ora portion thereof.

[0116] In general, embolism protection devices can be supplied tomedical professionals in a range of sizes, such that an appropriate sizecan be selected from the available sizes for a particular patient andfor a particular point of placement. Due to the expanding nature of theembolism protection device a precise size device is not required sincethe device conforms over a reasonable range to the vessel. Nevertheless,imaging techniques and estimates from experience and the patient's sizecan provide an appropriate estimate for the appropriate size of theembolism protection device. An embolism protection device can be placedwithin the desired vessel of a patient with a catheter, a syringe, aguidewire or the like. In particular, an embolism protection device canbe attached to a guidewire to feed the device through a catheter to adesired position in a vessel within a patient. The guidewire can beseparate from the device following the placement of the device, or theguidewire can remain tethered to the device to facilitate maintainingthe device at the desired position and/or to facilitate removal of thedevice. Removal of the guidewire can be performed by pulling out theguidewire if the guidewire is not attached to the device and if thedevice is applying sufficient force against the walls of the vessel suchthat friction can hold the device in place. If the guidewire is toremain attached to the device, the guidewire can be attached to thedevice with a mechanical attachment or with an adhesive. The guidewirecan be mechanically attached to the device, for example, by forming thepolymer around the end of the wire, generally with a non-straightsection of wire, winding the wire around a section of the device and/orheat strinking a portion of the polymer around the end of the wire.

[0117] Due to the potentially serious outcomes of cardiac interventionthat can result in emboli associated with the aorta, the embolismprotection device can be positioned at one or more positions within theaorta or in arteries branching from the aorta. Referring to FIG. 12,aorta 200 is shown adjacent heart 202. As shown in FIG. 12, fiveembolism protection devices 204, 206, 208, 210, 212 are shown indifferent positions. Any one or more of these can be used for aparticular patient. Devices 204-212 are shown with device 204 in theascending aorta, device 206 in the descending aorta, device 208 in theinnominate artery, device 210 in the left common carotenoid artery anddevice 212 in the left subclavian artery.

[0118] Referring to FIG. 13, an embodiment is shown that is appropriatefor use when the heart is on bypass. In particular, this device can beplaced in the aorta distal to the site of cross clamp in a cardiacsurgical procedure involving cardiopulmonary bypass. In this embodiment,an embolism protection device 220 is within the ascending aorta 222distal to cross clamp 224 and is attached to an aortic cannula 226, forexample, with a fastener 228, such as a loop of material, a clip,anchor, a catching device or the like. An aortic cannula generally canbe used to return blood to the heart when the heart is on bypass. Forexample, the heart can be placed on bypass during a procedure to repairportions of the heart. Aortic cannula are known in the art, and oneembodiment is described in U.S. Pat. No. 6,387,087 to Grooters, entitled“Aortic Cannula,” incorporated herein by reference. Attachment to aorticcannula 226 stabilizes device 220 at the pressures experienced duringthe cross clamp procedure. Referring to FIG. 14, release of cross clamp224 can result in the corresponding release of emboli 230 that aretrapped by embolism protection device 220. Device 220 can releasebioactive agents to dissolve emboli 230, and, additionally oralternatively, removal of device 220 can remove trapped emboli. Forexample, device 220 can be removed from the cannula site shortlyfollowing the removal of the cannula.

[0119] In some embodiments, an embolism protection device can be placedwithin a coronary artery. In particular, the embolism protection devicecan be placed down stream from a planned site of intervention, forexample, by angioplasty, placement of a bypass graft or introduction ofa stent. Referring to FIG. 15, embolism protection device 240 is shownwithin coronary artery 242 of heart 244. Device 240 is locateddownstream in the artery from an intervention site 246.

[0120] In other embodiments, an embolism protection device can be placein the venous side of the heart/vascular system to prevent emboli to thelungs. Referring to FIG. 16, embolism protection device 250 is withinthe pulmonary artery 252 downstream from the pulmonary heart valve 254where pulmonary artery 252 attached to heart 256. Flow from thepulmonary artery goes to the lungs. More generally, an embolismprotection device can be placed within any vessel in the body. As shownin FIG. 17, devices 260, 262 are within arteries leading to the leg fromthe descending abdominal aorta 264 while device 266 is in an arm.Embolism protection devices can be similarly placed in veins.

[0121] As noted above with respect to FIG. 12, the embolism protectiondevice can comprise two distinct portions or similarly can be used witha separate but associated drug delivery article. Use of such devices inthe context of the application of a stent is shown in FIGS. 18A, 18B and18C. As shown in FIG. 18A, a two component embolism protection device270 is placed downstream from a plaque deposit 272 in vessel 274. Inthis embodiment, device 270 comprises a tether 276 to facilitateremoval, although other removal approaches can be used. As shown in FIG.18B, a stent 278 has been applied to plaque deposit 272 with thepotential generation of emboli 280, which are trapped by embolismprotection device 270. As shown in FIG. 18C, an embolism trappingportion 282 of device 270 is being removed using tether 276, while abioactive agent eluting portion 284 of device 270 remains in vessel 274.

[0122] The elution of a bioactive agent from the embolism protectiondevice is described above. Additionally or alternatively, one or morebioactive agents can be delivered through a guidewire or the liketethered to the embolism protection device. The guidewire can have asmall inner channel that has an opening into the vessel at or near theproximal end. The flow rate and time determines the dose of biologicallyactive agent delivered into the vessel. Referring to FIG. 19, embolismprotection device 300 associated with guidewire 302 is within a bodyvessel 304. Guidewire 302 has a small internal channel that can have anopening at point A, B and/or C. The natural flow direction in the vesselis indicated by arrow 306. Delivery of a biologically active agent atpoint A results in the flow of the agent through device 300 anddownstream. Delivery of the agent at point B results in a concentrationof the agent within the device with any residual agent flowingdownstream. In addition, delivery of the agent at point C results indelivery of the agent downstream from the device.

[0123] Once the embolism protection device has served its purpose, itmay be desirable to remove the device or a portion thereof. For example,shortly after completing a procedure, the device may have had theopportunity to collect and/or dissolve the emboli of significance.Alternatively, once the embolism protection device has completed elutinga biologically active agent following the trapping and/or dissolving ofemboli associated with a procedure or other event, it may be desirableto remove the device. Removal of the device can take place, for example,minutes, hours, days, months or years following delivery depending onthe particular device and its intended purpose.

[0124] As noted above, in some embodiments, an embolism protectiondevice can be attached to one or more tethers or the like such thatpulling on the tethers tends to reduce the size of the device such thatit can be moved upstream from its delivered position. In otherembodiments, an embolism protection device can have a reduced diameteror pointed tip at the proximal end. With a reduced diameter proximal endand a compressible polymer structure generally possessed by the device,the device can be pulled within a sheath using a tether due to theforces applied to the device at the end of the sheath. Once the deviceis confined within the sheath, the device can be withdrawn from thevessel with the sheath.

[0125] In alternative or additional embodiments, an extraction devicecan be used to facilitate removal of the embolism protection device. Anextraction device comprises a gripper that can grip the embolismprotection device and reduce the diameter of at least a portion thereof.The gripper can be positioned within the vessel through a catheter orthe like. An actuating wire or other control device can connect thegripper with a control handle at the proximal end of the gripper deviceoutside of the patient. Thus, the gripper can be manipulated by a healthcare professional from outside of the patient using appropriatevisualization techniques, such as a fiber optic based visualizationsystems for minimally invasive surgical procedures.

[0126] An embodiment of a suitable gripper is shown in FIG. 20. Gripper310 has a gripping portion with four flexible arms 312 extending from ashaft 314. Shaft 314 can have a hollow core for threading the shaft overa guide-wire or the like. An outer shaft 316 can move in positionrelative to shaft 314. Outer shaft 316 can engage arms 312 and deflectthem toward the center of shaft 314. This deflection of arms 312 resultsin a gripping function. Thus, if arms 312 are positioned along the outersurface of an embolism protection device, the deflection of arms 312toward a center axis compresses the embolism protection devicecorrespondingly. This deflection can be continued until the gripper andthe embolism protection device has a small enough profile for removalfrom the vessel. For embodiments of an embolism protection device with aplurality of sections, gripper 310 can be used to facilitate removal ofa portion of the embolism protection device oriented toward the gripper.Furthermore, various other gripper configurations, including, forexample, some configurations developed for use with catheters for otherfunctions can be adapted for use in removing an embolism protectiondevice.

EXAMPLES Example 1 Synthesis of Hydrozel Grafted Polymer

[0127] This example demonstrates the synthesis of a polyacrylamidehydrogel polymer grafted onto a PET polyester polymer.

[0128] Medical grade PET fibers were surface activated by subjectingthem to an oxygen plasma. The plasma glow discharge system primarilyconsisted of a barrel radio frequency (RF) plasma reactor with adiameter and depth of six inches (Extended Plasma Cleaner, HarrickScientific, Ossining, N.Y.). The pressure was monitored by athermocouple vacuum gauge (Hastings Vacuum Gauge, DV-6). The reactionchamber was evacuated to 10 millitorr (mtorr) to remove contaminants andmoisture. The chamber was then flooded with research grade oxygen gas(99.99%), and evacuated until a constant pressure of 150 mtorr wasestablished, at which point RF plasma of 30Watt was applied for tenminutes. Activated fibers were then dip coated with a mixture ofpolyacrylamide (10% by weight (wt)), acrylamide monomer (10%-20% by wt),and methylenebis-acrylamide (0.05-0.1% by wt crosslinker) and a UVsensitive initiator in water. The grafting was allowed to cure under aUV lamp for 10 minutes.

[0129] Visual inspection and microscopic techniques verified matrixsynthesis. See FIGS. 21 and 22. The grafted copolymer matrix was thencharacterized using swelling control studies.

Example 2 Incorporation of Biological Agent into Hydrogel and ControlledRelease

[0130] This example demonstrates the incorporation of tPA into apolyacrylamide (PAM) polymer and the subsequent release of the tPA.

[0131] In this experiment, tPA was incorporated into a polyacrylamidehydrogel by dispersion into the polymerization solution at the time ofpolymerization. This method may result in the entrapment of the tPA inthe interstices of the gel-like matrix where it is held until hydrationat which time the agent is slowly released.

[0132] A 2.8 ml solution was prepared comprising 1.5 ml-5 weight %acrylamide solution (approximate final concentration based on a volumeper volume dilution 2.67% acrylamide), 6 μl-human two-chain tPA (2.2mg/ml, from Molecular Sciences, MI), 9 μl-10% ammonium persulfate, 2.25μl-TEMED (N,N,N′,N′-tetramethylenediamine, 99% solution) and deionizedwater. The ammonium persulfate produces free radicals faster in thepresence of TEMED such that the addition of TEMED to the mixtureaccelerates the polymerization and crosslinking of the gel. Threealiquots of 500 μl gels were made in glass test tubes and allowed topolymerize for 1 hr at room temperature (total tPA conc. 4.4 micromolarμM in each gel), thus creating three gels. Upon onset of polymerization,50 μl of the control samples were removed and kept at −80° C.

[0133] The release kinetics of the tPA was analyzed. Afterpolymerization, the gels were carefully removed from the test tubes andput in 20 ml vials. The test tube was rinsed with 5 ml of phosphatebuffered saline (PBS), and the rinse poured over the gel in the 20 mlvial. This was slightly shaken to rinse the gel and to remove anyunincorporated tPA. A 501 μl quantity of this solution was frozen. Theremainder was poured off and replaced with another 5 ml of PBS. Both thegels and the controls were kept at 4° C. for the release experiment inan effort to prevent protein degradation and slightly shaken on anoscillating shaker. At designated time points, 50 microliter (μl)aliquots of buffer were taken. The amount of tPA in each aliquot wasdetermined via ELISA (Diapharma Group, Inc. Westchester, Ohio). Inbrief, buffer samples were transferred in 100 μl volumes to wells of a96-well plate containing anti-tPA IgG. The samples were incubated for 2hours at room temperature. Bound tPA was detected with HRP (horseradishperoxidase)—labeled Fab fragments of anti-tPA IgG followed by aperoxidase substrate. Colorimetric staining was detected and actualquantity determined via comparison to the included standards (BiopoolInternational, Cat#101-442).

[0134]FIG. 23 shows the standard curve for the tPA ELISA. The curve waslinear over the range tested with an R-squared value of 0.978. FIG. 23is a plot of the experimentally measured time release kinetics of tPAfrom the hydrogel. Release of tPA from the hydrogel reached a maximumrelease of 31.4 ng/ml at 60 minutes.

[0135] We have demonstrated the ability to reliably produce a PET:PAMcopolymer matrix. This matrix can be produced such that swelling israpid, sustained and reproducible. In addition, tPA can be incorporatedinto the matrix. The release rate is typical of a hydrogel with aninitial quick release sustained for at least 60 minutes following testinitiation. This time duration would be sufficient forpost-cardiopulmonary bypass cross-clamp embolism protection devicefiltration time, however further crosslinking alterations can be made toalter release. This release can be tailored after the toxic doseparameters and dose necessary for emboli destruction are determined.

Example 3 In Vitro Emboli Dissolution Test

[0136] This example demonstrates the effectiveness of recombinant humanTissue Plasminogin Activator (tPA) as a resolving agent with respect tothe dissolution of porcine thrombolytic emboli in vitro.

[0137] tPA was diluted in phosphate buffered saline at the followingconcentrations: 1,000 nanograms/milliliter (ng/ml), 500 ng/ml, 100 ng/mland 0 ng/ml. The emboli dissolution potential of each tPA solution wasmeasured by applying the tPA solution to glass slides containing emboliand then measuring the change in emboli size as a function of time. Tocreate the emboli, coagulated porcine whole blood was placed in a 5 ccsyringe. Coagulated blood was extruded from the syringe and cut touniform size (200-225 μm diameter); these uniform coagulated bloodfragments will be referred to as “emboli”. Emboli were placed on glassslides for microscopic measurement. Samples were labeled andmeasurement/descriptions were made for each embolus. Measurement wasaccomplished with a Zeiss® Microscope and Zeiss® LSM 4 software forimage acquisition. One ml quantities of tPA solution were added to thecharacterized emboli and then placed on a shaker at 20 RPM in a testingroom at 30-35° C.

[0138] Emboli size measurements were taken at various time points.Results are reported in Table 1 below. TABLE 1 Decrease in Geometricsize tPA Sample concentration # pre Post % change 0 ng/ml 1 233.0 231.00.86 0 ng/ml 2 215.0 229.0 6.51 0 ng/ml 3 216.0 223.0 3.24 0 ng/mlaverage 221.3 227.7 2.86 100 ng/ml 11 222.0 216.0 −2.70 100 ng/ml 12180.0 200.0 11.11 100 ng/ml 13 176.0 173.0 −1.70 100 ng/ml average 192.7196.3 1.90 500 ng/ml 51 221.0 201.0 −9.05 500 ng/ml 52 189.0 162.0−14.29 500 ng/ml 53 221.0 190.0 −14.03 500 ng/ml average 210.3 184.3−12.36 1000 ng/ml 101 230.0 155.0 −32.61 1000 ng/ml 102 228.0 150.0−34.21 1000 ng/ml 103 177.0 146.0 −17.51 1000 ng/ml average 211.7 150.3−28.98

[0139] Thus, the tPA was effective at reducing thrombus size significantamounts.

Example 4 Evaluation with an in vitro Flow Loop

[0140] This example demonstrates the utility of an in vitro flow loopfor evaluation of an embolism protection device as well as provides anevaluation of two embodiments of an embolism protection device, one withtPA and one without tPA.

[0141] The interrupted flow loop was developed to mimic the environmentof a native coronary artery. The apparatus consisted of four components:a circulation unit, the embolism protection device, the blood/media, andthe emboli. The flow loop was constructed as indicated in FIG. 24. Thecirculation unit had a heated reservoir 350 holding blood and media 352,tubing 354, a pump 356, injection ports 358, 360 and a collection vessel362. Embolism protection device 364 was held in a fixture 366 withintubing 354. Flow through the system is noted in FIG. 24 with four flowarrows.

[0142] Embolism protection device 364 was formed with two sections ofstructure. The layered system for purposes of this experiment was apolymeric construct that could both release tPA and trap the embolibased on an appropriate porosity. Referring to a schematic view of apre-hydrated device 364 in FIG. 26, a first layer 380 was a nylon meshpolymer with a 70 micron pore diameter obtained from Sefar America Inc.Depew, N.Y. Layer 380 served to entrap emboli. A second layer 382 was asponge-like layer made of polyacrylamide and impregnated with tPA. Toincorporated tPA into layer 382, a solution was prepared comprising of1.5 ml-5 weight % acrylamide solution (approximately 2.67% acrylamidefinal concentration based on a volume per volume dilution), 6 μl- humansingle-chain tPA (2.2 mg/ml, Molecular Sciences, MI), 9 μl-10% ammoniumpersulfate and 6.7 μl-TEMED. Three aliquots of 0.5 ml gels were made inglass test tubes and allowed to polymerize for 1 hr at room temperature,thus creating three gels. Following polymerization, each gel had a totalTPA amount of 500 ng at a concentration of 1,000 ng/ml). The gels wereremoved from the tubes, and the nylon mesh layer was wrapped around theflat end and the sides of each gel leaving the rounded end of the gelfrom the bottom of the tube uncovered with the mesh. Each device whenplaced within the flow loop was positioned with the flat end down-streamand with the round end upstream such that emboli are trapped by the meshwithin the gel. Following contact with an aqueous solution, the gelexpands to approximately twice its volume, as is schematically shown inFIG. 27, while the nylon mesh remains essentially unchanged, although itexpands in response to the expansion of the gel. Due to the expansion ofthe gel, the pore size of the mesh may enlarge, but this enlargement wasnot directly measured.

[0143] Three two-layer embolism protection devices were constructed withtPA incorporation, and three two-layer devices were constructed withouttPA incorporation using the solution described above except with no tPA.For these tests, a selected device 364 held by the test fixture 366.Referring to FIG. 28, test fixture 366 has two rings 368, 370 heldtogether with a joining ring 372. Edges of device 364 are grippedbetween rings 368, 370 to fix device 364 in place.

[0144] Circulation of the media was performed with a centrifugal pumpcapable of generating flows from 30-120 ml/min. The tubing was a vinylpolymer with an inner diameter from 4-6 mm, similar to that of thenative arterial vessels. The experiment was accomplished in a testchamber at 37° C. Injection port 358 upstream from the embolismprotection device was used to introduce the test emboli. The mediumflowing through the system was phosphate buffered saline. Emboli weregenerated by placing 1 ml of pig animal blood in a syringe and allowingit to clot (see above for determination of emboli size). The flow loopwas validated using a calibrated flowmeter.

[0145] The emboli were introduced into the flow system at aconcentration of approximately 15 emboli/ml of buffered saline. The timeline for the testing was as follows:

[0146] 0 time—introduction of device

[0147] 1 sec.—Begin flow of media (buffered saline)

[0148] 10 sec—Measure flow rate

[0149] 15 sec—Inject emboli

[0150] 30 sec—Collect aliquot #1 (of effluent, i.e. media past device.)

[0151] 60 sec—Collect aliquot #2

[0152] 100 sec—Collect aliquot #3

[0153] 200 sec—Collect aliquot #4

[0154] 300 sec—Collect aliquot #5

[0155] After about five minutes, the flow was stopped and the deviceremoved and photographed microscopically. The device was then fixed forhistological analysis. Aliquots of collected liquid were analyzed foremboli. The fixed device was snap frozen, sectioned and placed on aslide for histological analysis. Sections were stainedimmunohistochemically for fibrin and platelet markers.

[0156] As described above, six prototypes for each design (3 with tPAand 3 without tPA) were loaded in the flow loop. Emboli entrapment anddissolution was evaluated in three different ways. First, flowmeasurements were made at different flow rates to determine the degreeto which the device retarded flow. Results are outlined in the followingtable. TABLE 2 Prototype No Device Media Mesh Only Device 30 ml/min 30.3± 0.6  30.0 ± 1.0  28.7 ± 0.6  60 ml/min  60 ± 0.0 59.3 ± 0.6  58.3 ±1.5  120 ml/min 119.7 ± 0.6  117.3 ± 2.5  114.3 ± 2.1  (120 ml/min) #1#2 #3 Samples w/out tPA 118 116 115 tPA 117 115 112

[0157] Second, the PBS was collected. The total collected effluent waspassed over a 0.22 gm filter, and the filter was analyzed via lightmicroscopy for presence of emboli. The effluent had no observable emboliafter passing through any of the six devices. This demonstrated that thedevices were effective to trap the emobli without blocking the flow.

[0158] Third, a portion of the embolism protection device was frozen andparaffin embedded for histological archiving. Selected samples weresectioned and prepared for immunohistochemistry as follows. Sectionswere postfixed for 2 minutes in 100 mmol/L tris-buffered 1%paraformaldehyde containing 1 mmol/L EDTA, pH 7.2, and rinsed with threechanges of phosphate buffered saline, pH 7.2. Porcine fibrindecomposition via tPA thrombolysis was detected using murine antibodiesspecific for neotype beta-chain fibrin (Mouse Anti-Human, Cross-reactswith pig, American Diagnostica, Inc., Greenwich, Conn., Cat 350, 1:100dilution, rhodamine conjugated, monoclonal IgG-1) and CD41 plateletglycoprotein IIa/IIIb (Mouse Anti-Human, Cross-reacts with pig,DakoCytomation, Carpinteria, Calif., Cat M7057, 1:100 dilution, FITCconjugated, monoclonal IgG-1). The antibodies listed above were dilutedin phosphate buffered saline containing 5% bovine serum albumin (SigmaChemical Co.) and applied to sections for 30 minutes. Then, the sectionwas rinsed with phosphate buffered saline. All sections werecover-slipped with a 1:8 dilution of Vectashield-DAPI(4,6-diamidino-2-phenylindole) in phosphate buffered saline (VectorLaboratories) and evaluated using an epifluorescence microscope.

[0159] Stained fibrin was analyzed and scored on a scale of 1-5; 1 beingfully intact and 5 being fully dissociated (see sample FIG. 29.). FIGS.29A and 29B are fibrin recovered from the embolism protection devicereleasing tPA, while FIGS. 4C and 4D show fibrin at the samemagnification recovered from an embolism protection device not releasingtPA. As seen in FIGS. 29A and 29B, fibrin treated with tPA was dissolvedaway to remove significant portions of the structure and to leaverelatively large pores in comparison with the equivalent fibrin in FIGS.29C and 29D that was not treated with tPA.

[0160] The values of the scoring are given in Table 2. Results clearlyshow degradation of the emboli associated with the device in the treatedgroup and intact emboli in the devices which were not prepared with thetPA. These results show that the tPA eluting from the devices waseffective to shrink the emboli.

[0161] The embodiments described above are intended to be exemplary andnot limiting. Additional embodiments are within the claims. Although thepresent invention has been described with reference to preferredembodiments, workers skilled in the art will recognize that changes maybe made in form and detail without departing from the spirit and scopeof the invention.

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What is claimed is:
 1. An embolism protection device comprising aplurality of fibers having surface capillaries, wherein the fibers arebound within a structure and have a deployed configuration that fillsthe lumen of a vessel having a diameter corresponding to that of a humanvessel.
 2. The embolism protection device of claim 1 wherein fiberscomprise a hydrophilic polymer.
 3. The embolism protection device ofclaim 1 wherein the fibers comprise polyester.
 4. The embolismprotection device of claim 1 wherein the fibers comprise a bioresorbablepolymer.
 5. The embolism protection device of claim 1 wherein the fibersare within a fabric.
 6. The embolism protection device of claim 1wherein the fibers are curled.
 7. The embolism protection device ofclaim 1 wherein the fibers have a curled configuration at bodytemperature.
 8. The embolism protection device of claim 1 wherein thefibers are in a bundle.
 9. The embolism protection device of claim 1wherein the fibers are grafted with a second polymer.
 10. The embolismprotection device of claim 9 wherein the second polymer is a hydrogel.11. The embolism protection device of claim 1 wherein the structurewithin the vessel has an effective pore size to trap a majority ofemboli with a diameter larger than 0.2 mm while a majority ofparticulates with a diameter smaller than 0.001 mm pass.
 12. Theembolism protection device of claim 1 further comprising a biocompatibleadhesive.
 13. The embolism protection device of claim 1 furthercomprising a tether.
 14. A method for trapping emboli, the methodcomprising placing an embolism protection device of claim 1 within apatient's vessel.
 15. A system for trapping emboli comprising a deliverytool comprising a tether and an embolism protection device attached tothe tether and wherein the embolism protection device comprises a fiberwith surface capillaries with a size suitable for placement within ahuman vessel.
 16. The system of claim 15 wherein the tether is aguidewire.
 17. The system of claim 15 wherein the delivery toolcomprises a cannula through which the embolism protection device can bedelivered.
 18. The system of claim 15 wherein the fibers comprise apolyester.
 19. The system of claim 15 wherein the embolism protectiondevice is attached to the tether with an adhesive.
 20. A method fortrapping emboli, the method comprising placing a fiber within apatient's vessel wherein the fibers have surface capillaries.
 21. Themethod of claim 20 wherein a plurality of fibers with surfacecapillaries are placed within the patient's vessel.
 22. The method ofclaim 21 wherein the plurality of fibers are in a bundle.
 23. The methodof claim 20 wherein the placing of the fiber is performed with adelivery tool that associates with the fiber.
 24. The method of claim 23wherein the delivery tool holds the fiber in a configuration for passagethrough a sheath for deployment of the fiber within a vessel.
 25. Themethod of claim 24 wherein a plurality of fibers are deployed and theplurality of fibers fill the lumen of the vessel with an effective poresize to trap a selected range of emboli.
 26. The method of claim 25wherein the delivery tool comprises a guidewire.
 27. The method of claim20 wherein the fiber is curled at body temperature.